WO2012116364A1 - Vibrométrie ultrasonique avec ultrasons non focalisés - Google Patents

Vibrométrie ultrasonique avec ultrasons non focalisés Download PDF

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Publication number
WO2012116364A1
WO2012116364A1 PCT/US2012/026769 US2012026769W WO2012116364A1 WO 2012116364 A1 WO2012116364 A1 WO 2012116364A1 US 2012026769 W US2012026769 W US 2012026769W WO 2012116364 A1 WO2012116364 A1 WO 2012116364A1
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Prior art keywords
ultrasound
subject
unfocused
measurement data
recited
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PCT/US2012/026769
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English (en)
Inventor
James F. Greenleaf
Shigao Chen
Armando Manduca
Pengfei Song
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Mayo Foundation For Medical Education And Research
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Priority to KR1020137025285A priority Critical patent/KR101929198B1/ko
Priority to CN201280020131.5A priority patent/CN103492855B/zh
Priority to JP2013555633A priority patent/JP6067590B2/ja
Priority to US14/001,604 priority patent/US11172910B2/en
Priority to EP12749825.1A priority patent/EP2678658B1/fr
Priority to BR112013021791-0A priority patent/BR112013021791B1/pt
Publication of WO2012116364A1 publication Critical patent/WO2012116364A1/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N9/00—Investigating density or specific gravity of materials; Analysing materials by determining density or specific gravity
    • G01N9/24—Investigating density or specific gravity of materials; Analysing materials by determining density or specific gravity by observing the transmission of wave or particle radiation through the material
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/485—Diagnostic techniques involving measuring strain or elastic properties
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
    • A61B8/5223—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for extracting a diagnostic or physiological parameter from medical diagnostic data
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N29/00—Investigating or analysing materials by the use of ultrasonic, sonic or infrasonic waves; Visualisation of the interior of objects by transmitting ultrasonic or sonic waves through the object
    • G01N29/04—Analysing solids
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N29/00—Investigating or analysing materials by the use of ultrasonic, sonic or infrasonic waves; Visualisation of the interior of objects by transmitting ultrasonic or sonic waves through the object
    • G01N29/04—Analysing solids
    • G01N29/07—Analysing solids by measuring propagation velocity or propagation time of acoustic waves
    • G01N29/075—Analysing solids by measuring propagation velocity or propagation time of acoustic waves by measuring or comparing phase angle
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N29/00—Investigating or analysing materials by the use of ultrasonic, sonic or infrasonic waves; Visualisation of the interior of objects by transmitting ultrasonic or sonic waves through the object
    • G01N29/22—Details, e.g. general constructional or apparatus details
    • G01N29/221—Arrangements for directing or focusing the acoustical waves
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N29/00—Investigating or analysing materials by the use of ultrasonic, sonic or infrasonic waves; Visualisation of the interior of objects by transmitting ultrasonic or sonic waves through the object
    • G01N29/22—Details, e.g. general constructional or apparatus details
    • G01N29/24—Probes
    • G01N29/2456—Focusing probes
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/4808—Multimodal MR, e.g. MR combined with positron emission tomography [PET], MR combined with ultrasound or MR combined with computed tomography [CT]
    • G01R33/4814—MR combined with ultrasound
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52023—Details of receivers
    • G01S7/52036—Details of receivers using analysis of echo signal for target characterisation
    • G01S7/52042—Details of receivers using analysis of echo signal for target characterisation determining elastic properties of the propagation medium or of the reflective target
    • G—PHYSICS
    • G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
    • G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
    • G16H50/00—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics
    • G16H50/30—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics for calculating health indices; for individual health risk assessment
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/46—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient
    • A61B8/461—Displaying means of special interest
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2291/00—Indexing codes associated with group G01N29/00
    • G01N2291/02—Indexing codes associated with the analysed material
    • G01N2291/024—Mixtures
    • G01N2291/02475—Tissue characterisation
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2291/00—Indexing codes associated with group G01N29/00
    • G01N2291/02—Indexing codes associated with the analysed material
    • G01N2291/028—Material parameters
    • G01N2291/02827—Elastic parameters, strength or force
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2291/00—Indexing codes associated with group G01N29/00
    • G01N2291/04—Wave modes and trajectories
    • G01N2291/042—Wave modes
    • G01N2291/0422—Shear waves, transverse waves, horizontally polarised waves
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8909—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration
    • G01S15/8915—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array
    • G01S15/8927—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array using simultaneously or sequentially two or more subarrays or subapertures

Definitions

  • the field of the invention is systems and methods for ultrasound. More particularly, the invention relates to systems and methods for ultrasound vibrometry, in which ultrasound is used to measure mechanical properties of a material or tissue of interest.
  • tissue mechanical properties particularly the elasticity or tactile hardness of tissue
  • Characterization of tissue mechanical properties has important medical applications because these properties are closely linked to tissue state with respect to pathology.
  • breast cancers are often first detected by the palpation of lesions with abnormal hardness.
  • a measurement of liver stiffness can be used as a noninvasive alternative for liver fibrosis staging.
  • Shear wave speeds at a number of frequencies are measured by pulse echo ultrasound and subsequently fit with a theoretical dispersion model to inversely solve for tissue elasticity and viscosity. These shear wave speeds are estimated from the phase of tissue vibration that is detected between two or more points with known distance along the shear wave propagation path.
  • the present invention overcomes the aforementioned drawbacks by providing a method for measuring a mechanical property of a subject with an ultrasound system using unfocused ultrasound energy.
  • the method includes applying unfocused ultrasound energy to a subject in order to produce a plurality of tissue deformations therein at a plurality of axial depths.
  • Measurement data is then acquired from the subject by applying ultrasound energy to at least one location in the subject at which at least one of the plurality of tissue deformations is located.
  • a mechanical property of the subject is calculated using this acquired measurement data.
  • the ultrasound transducer is used to produce shear waves that propagate in the subject in at least one direction extending outward from the ultrasound transducer by applying ultrasound energy to the subject such that the ultrasound energy produces a force in the direction substantially normal to the surface of the ultrasound transducer.
  • Measurement data is acquired by applying ultrasound energy to at least one location in the subject in which the shear waves are present.
  • a mechanical property of the subject is then calculated using the acquired measurement data.
  • At least one of the produced shear waves is a spherical wave that propagates radially outward from a point on a surface of the ultrasound transducer.
  • FIG. 1 is a pictorial representation of an example of a focused ultrasound beam that produces shear waves propagating outward from the focused ultrasound beam at a focus depth;
  • FIG. 2 A is a pictorial representation of an example of an unfocused ultrasound beam that produces shear waves propagating outward from and inward into a region of insonification produced in response to the unfocused ultrasound;
  • FIG. 2C is a pictorial representation of a two-dimensional array ultrasound transducer for imaging out-of-plane shear waves
  • FIG. 2D is a pictorial representation of two ultrasound transducers used for imaging out-of-plane shear waves; and [0027] FIG. 3A is a pictorial representation of an example of an unfocused ultrasound beam generated by a curvilinear transducer array that produces shear waves propagating outward from a region of insonification produced in response to the unfocused ultrasound;
  • FIG. 3B is a pictorial representation of an example of an unfocused ultrasound beam generated by a curvilinear transducer array that produces shear waves propagating outward from and inward into a region of insonification produced in response to the unfocused ultrasound;
  • FIG. 4B is a pictorial representation of an example of an unfocused ultrasound beam generated off-center of a curvilinear ultrasound transducer to produce shear waves propagating outward from a region of in sonification produced in response to the unfocused ultrasound;
  • FIG. 5 is a pictorial representation of an example of two unfocused ultrasound beams generated off-center of an ultrasound transducer to produce shear waves propagating outward from respective regions of insonification produced in response to the unfocused ultrasound, such that the shear waves interact within an object or subject disposed between said unfocused ultrasound beams;
  • FIG. 6 is a pictorial representation of an example of an apodized, unfocused ultrasound beam generated that produces shear waves propagating outward from a region of insonification produced in response to the unfocused ultrasound;
  • FIG. 7 is a pictorial representation of an example of an unfocused ultrasound beam used to produce shear waves propagating away from an ultrasound transducer in response to the unfocused ultrasound;
  • FIG. 8 is a pictorial representation of an example of two unfocused ultrasound beams produced in accordance with some embodiments of the present invention.
  • FIG. 9 is a pictorial representation of an example of multiple unfocused ultrasound beams being used to chase and amplify a propagating shear wave in accordance with some embodiments of the present invention.
  • FIGS. lOA-lOC are pictorial representations of examples of methods for measuring shear wave propagation using focused ultrasound detection beams;
  • FIGS. 11A-11C are pictorial representations of examples of methods for using a plurality of unfocused ultrasound beams arranged in a comb pattern to produce shear waves in accordance with some embodiments of the present invention
  • FIG. 1 ID is a pictorial representation of two groups of shear waves that propagate in different directions and that are produced using comb push pulses, such as those illustrated in FIGS. 11A-11C;
  • FIG. 1 an example of a previous focused ultrasound configuration is illustrated.
  • a focused ultrasound beam 102 is produced by an ultrasound transducer 104.
  • shear waves 106 are generated. These shear waves propagate along a propagation direction 108 that emends outward from a push axis 110.
  • FIG. 2A an example of a region of insonification 202 produced by unfocused ultrasound energy, such as a tone burst, generated by an ultrasound transducer 204 is illustrated.
  • the region of insonification 202 has a thickness that depends on the in-plane size of the transducer elements and a width that depends on the total width of the transducer elements used for insonification.
  • This ultrasound energy produces a radiation force throughout the region of insonification 202.
  • This radiation force causes region of insonification 202 to move towards or away from the transducer 204.
  • shear waves 206 are produced and propagate along a propagation axis 208 that is normal to the edge of the region of insonification 202.
  • the shear waves 206 propagate in two directions, outward from the region of insonification 202 and inward toward the center of region of insonification 202.
  • Some shear waves 206 propagate in the out-of -plane direction with respect to the ultrasound transducer 204 and, therefore, cannot be imaged by a one-dimensional transducer, such as the one shown in FIG. 2A.
  • a higher- dimensional transducer such as a two-dimensional transducer.
  • shear waves 206 are produced along the full extent of the region of insonification 202.
  • multiple parameters may be varied to make imaging consistent with the desired task.
  • a wide range of parameters can be varied in order to tailor the imaging at hand.
  • the unfocused ultrasound beam is narrow, out-of-plane shear waves will no longer be plane waves; rather, the shear waves will be similar to a cylindrical wave emanating from the narrow ultrasound beam.
  • shear wave measurements were limited to the ultrasound axial depth corresponding to the focus depth, d j .
  • shear waves generated by unfocused ultrasound are relatively uniform along the ultrasound axial depth. Therefore, measurements can be made at all axial depths, and not just one prescribed depth, such as the focus depth in focused ultrasound techniques.
  • FIG. 2C another example of how unfocused ultrasound may be used to generate propagating shear waves or other tissue deformation is illustrated.
  • multiple collinear elements in a two-dimensional ultrasound transducer array 252 are energized to produced a planar ultrasound beam that is unfocused along an axis of the ultrasound trans ducer.
  • one or more columns of transducer elements 254 may be energized to produce a planar ultrasound beam 256 that is unfocused along the column direction of the transducer 252.
  • a small delay may be introduced across the columns 254 to simulate the acoustic lens on a one-dimensional transducer. These small delays will result in elevational focusing.
  • the shear waves produced by a focused ultrasound beam will be similar to a cylindrical wave emanating from the narrow ultrasound beam 102. Therefore, the amplitude of the shear wave decreases rapidly as it propagates outwards from the push axis 110 because the shear wave energy is distributed over a larger area as the wave propagates outwards from the push axis 110. This effect can be called “geometric attenuation.”
  • the out-of-plane shear wave produced in FIG. 2C is close to a planar shear wave and, therefore, is not subject to geometric attenuation.
  • the out-of-plane shear wave such as the one illustrated in FIG. 2C, can propagate over longer distances, which is highly advantageous because shear waves produced by ultrasound are usually very weak and can only propagate over a very short distance.
  • a small push transducer 272 can be attached to one side of the transducer array 270, as illustrated in FIG. 2D.
  • the out-of-plane shear wave can then be detected by the one-dimensional array transducer 270.
  • the push transducer 272 may be a single element transducer with a fixed elevational focus.
  • the push transducer 272 can be clipped to the one-dimensional array transducer 270 and fired by a single signal source through an external amplifier.
  • An example of a signal source is the signal from a continuous-wave Doppler probe port of an ultrasound scanner.
  • a second push transducer can be attached to the other side of the one-dimensional array transducer 270 to produce out- of-plane shear waves from both sides.
  • a region of insonification 302 can also be produced by unfocused ultrasound energy generated by a curvilinear array transducer 304.
  • a narrow unfocused beam and a wide unfocused beam can generate different shear wave propagation patterns as shown in FIGS. 3A and 3B.
  • the center of the region of insonification 302 under the curvilinear array transducer 304 will see two shear waves crossing each other at an angle. This effect can be used for angle compound imaging.
  • the unfocused beam does not need to be produced from the center of the transducer as shown in FIGS. 2A-3B above. Rather, the unfocused ultrasound energy can be transmitted off-center from the transducer, as shown in FIGS. 4A and 4B.
  • unfocused ultrasound energy can be produced as a single beam, or as a pair of beams, that is transmitted to either side, or both sides, of the ROI 510.
  • the generated shear waves will propagate across the ROI 510, thereby facilitating estimations of the shear wave speed in the ROI 510.
  • Polarization of the shear wave 714 is in the direction extending away from the transducer 704 along the propagation axis 716 and, therefore, the shear wave 714 can be detected by the same ultrasound transducer 704, This effect can be used to interrogate the tissue in a longitudinal direction extending away from the transducer 704 rather than the lateral direction illustrated in FIGS. 1-6.
  • This technique can be additionally useful for angle compounding. It is noted that the so-called "Fibroscan" studies shear waves in this longitudinal angle; however, there is an important distinction between the Fibroscan method and the method presented herein.
  • shear waves are generated by mechanically vibrating a transducer with an external shaker, whereas the present method generates shear waves by transmitting ultrasound energy, such as tone bursts of unfocused ultrasound energy, without the need for a specialized mechanical vibrator.
  • ultrasound energy such as tone bursts of unfocused ultrasound energy
  • focused ultrasound may also be used to produce shear waves that propagate away from the transducer, similar to the aforementioned technique.
  • unfocused ultrasound energy can also be used to achieve the desired result.
  • two unfocused ultrasound energy beams may be produced in close proximity to each other, such that unique patterns of shear waves are generated in a region between those unfocused ultrasound beams.
  • more than one tone burst of unfocused ultrasound energy can be used to follow the propagation of a shear wave as it travels through different locations.
  • an ultrasound beam can be transmitted to produce a first region of insonification 902a at a time, t and a location, j, to generate a shear wave 906a.
  • another ultrasound beam can be transmitted to produce a second region of insonification 902b at a time, t 2 , and a location, X 2 ⁇
  • the location, x 2 is selected to be the location at which the shear wave 906a arrives at the time, t 2 .
  • the results of the application of the second ultrasound energy is the production of a shear wave 906b that has a higher amplitude than shear wave 906a.
  • the detection and measurement of shear waves can be achieved with both traditional focused ultrasound, or by plane wave flash imaging. Flash imaging generates a two-dimensional image with a single unfocused ultrasound transmission and, therefore, can be used to produce a time s;eries of images of shear wave propagation in two dimensions. If properly processed, this time series of images can generate a two-dimensional elasticity image from just one ultrasound push. Focused ultrasound beams are limited to tracking motion along the ultrasound ray 1018; therefore, such shear wave detection is not as flexible. However, an average shear wave speed can still be estimated along the ultrasound beam axis using the arrival time of shear waves propagating through the distances /j , r 2 , or (r— r 2 ) , as illustrated in FIGS. lOA-lOC.
  • Shear waves from different unfocused push beams interfere with each other constructively and destructively and eventually fill the entire field-of-view (“FOV”).
  • a directional filter is used to extract left-to-right (“LR”) propagating shear waves and right-to-left (“RL”) propagating shear waves from the interfering shear wave patterns.
  • LR left-to-right
  • RL right-to-left
  • a time-of-flight based shear wave speed estimate method may be used to recover local shear wave speed at each pixel from both LR waves and RL waves.
  • a final shear wave speed map may then be combined from the LR speed map and RL speed map.
  • FIGS. 11A-11C multiple unfocused push beams that are spatially spaced apart, similar to a "comb" pattern, can be utilized for shear wave generation.
  • a comb-push field 1102 will generate higher SNR shear wave motions throughout the entire region under the aperture of the transducer 1104.
  • a single comb- push can also generate shear waves lasting for a long time at any given spatial location because shear waves from different push beams in the comb arrive at different times. The combined effect is that strong shear wave signals covering the entire spatial and time domain are produced, which can improve the SN R and, therefore, the reliability of direct inversion.
  • the comb-push pulses illustrated in FIGS. 11A-11C are shown to be composed of evenly spaced pulses, it will be appreciated by those skilled in the art that the comb push pulse can also be composed of unevenly spaced push pulses.
  • the elements of an array transducer 1104 such as a linear array transducer, used to produce push beams are divided into a number of subgroups, as shown in FIG. 11A.
  • the elements may be divided into nine subgroups and labeled from subgroup one to nine.
  • Each subgroup of push beam looks like a tooth of a comb, thus this kind of push pulse is referred to as a "comb-push.”
  • comb-push As an example, when five subgroups are used to form a comb-push it may be called a "5 -tooth comb-push.”
  • Each unfocused beam in the CUSE imaging technique generates two shear wave fronts propagating towards opposite directions.
  • one shear wave front may propagate left-to-right (“LR" ⁇ and the other right-to-left (“RL”).
  • Shear waves from different subgroups of the comb-push constructively and destructively interfere with each other, and a complicated shear wave field is created as a result.
  • the destructive interference decreases the amplitude of the shear wave motion measured for shear wave velocity estimates.
  • a directional filter may be used. Examples of directional filters that are useful for this purpose are described, for example, by T. Deffieux, et al., in “On the Effects of Reflected Waves in Transient Shear Wave Elastography,” IEEE Trans Ultrason Ferroelectr Freq Control, 2011; 58:2032-2305.
  • a comb push with a motion detection ultrasound beam 1120 placed outside the comb Shear waves from different push beams 1102 of the comb arrive at the detection beam 1120 position at different times because the propagation distance is different for each push beam 1102. Therefore, the detected shear wave signal 1106 will have multiple peaks along the time axis. Shear wave speed of the medium can be calculated from the time interval between these peaks, or by the frequency of the detected time signal, and the distance, r, between the push beams 1102 of the comb.
  • McAleavey also taught placing the detection beam outside the spatially modulated field.
  • a detection beam 1120 can be placed within the comb push field 1102. If all the push beams 1102 are placed symmetric about the detection beam 1120, shear waves 1106 from left side push beams 1102 will arrive at the detection beam 1120 at the same time as the shear waves 1106 from the push beams 1102 to the right side of the detection beam 1120. As a result, these shear waves 1106 add constructively and the shear wave magnitude is doubled. Shear wave amplitude is, thus, increased, leading to higher SNR for shear wave speed estimation.
  • Shear wave speed may be estimated using the time-of-flight algorithm by cross-correlating recorded particle velocity profiles along the lateral direction.
  • two points separated by eight ultrasound wavelengths e.g., eight pixels
  • the particle velocity profiles may be Tukey windowed so that both ends of the signal are forced to be zero, thereby facilitating more robust cross-correlation.
  • the velocity profiles may also be interpolated before cross-correlation. As an example, the velocity profiles may be interpolated by a factor of five.
  • One advantage of CUSE imaging is that only one data acquisition is required to reconstruct a full FOV two-dimensional shear wave speed map.
  • This advantage is described now with respect to the example configuration illustrated in FIG. 11D, where an ultrasound transducer 1104 is used to produce a first group of shear waves 1152 propagating in a first direction 1154 and a second group of shear waves 1156 propagating in a second direction 1158.
  • the first direction may be a left-to-right (“LR") direction and the second direction may be a right-to-left (“RL"] direction.
  • the shear waves in the first group 1152 will propagate under subgroups SG2-SG9 and the shear waves in the second group 1156 will propagate under subgroups SG1-SG8.
  • the shear wave speed at these areas can be recovered.
  • the shear waves in the first group 1152 cannot cover the area under subgroup SGI and the shear waves in the second group 1156 cannot cover the area under subgroup SG9. Therefore, a combination method is used to combine the shear wave speed map for the first group of shear waves 1152 and the shear wave speed map for the second group of shear waves 1156 so that a full FOV speed map can be obtained.
  • the region under subgroup SGI is reconstructed using only the second group of shear waves 1156 and region under subgroup SG9 is reconstructed using only the first group of shear waves 1152.
  • the regions 1160 under subgroups SG2-SG8 are reconstructed by averaging the shear wave speed estimates from both the first group of waves 1152 and the second group of wave 1156.
  • ultrasound push beams that are generated perpendicular, or substantially perpendicular, to the ultrasound transducer surface
  • the ultrasound push beams may also be steered such that they are not normal to the transducer surface.
  • directional filtering may be modified to extract shear waves travelling at arbitrary angles.
  • An example of using directional filters for arbitrary angles is described by A. Manduca, et al., "Spatio-Temporal Directional Filtering for Improved Inversion of MR Elastography Images," Medical Image Analysis, 2003; 7:465-473.
  • An advantage of using unfocused ultrasound energy to produce shear waves as described herein is that very few transduce r elements need to be energized. Therefore, the transmit board does not need to produce a great deal of energy in order to produce a great deal of power on each of the transducer elements.
  • the result of this is that the ultrasound push can be very long without overtaxing the transmit board because so few elements are used and because there is no need to have a large aperture to make a focus at some depth in the tissue.
  • a focused ultrasound beam can easily exceed the FDA limits for diagnostic ultrasound and, therefore, a focused push tone burst cannot use the full voltage deliverable by the ultrasound system.
  • the intensity of the ultrasound energy is low for the meth od described herein because the beam is not focused.
  • the mechanical index and intensity of the ultrasound beam should be well below the FDA limits.
  • very high voltage can be used to produce the ultrasound push beams, which in turn can produce larger tissue motions.
  • Another advantage of the herein described method is that because the mechanical index is low and because the intensity is low, the shear waves can be induced at a high pulse repetition rate, thereby allowing for many measurements in time, which is advantageous for dynamic measurements, such as through the cycle of the heart.
  • tissue motion generated by a unfocused beam may be low compared to that generated by a focused beam. Therefore the SNR for shear wave detection may not be as high.
  • tissue motion generated by a unfocused beam may be low compared to that generated by a focused beam. Therefore the SNR for shear wave detection may not be as high.
  • higher transmit voltages can be used to obtain larger tissue motions because it is unlikely that an unfocused ultrasound beam will exceed FDA limits on intensity.
  • a much longer tone burst can be transmitted to produce larger tissue motion because a unfocused beam uses fewer transmit elements and less energy; thus, power droop of the transmit board is less of an issue.
  • a running average along the depth of the ultrasound beam can be used to improve the SNR of shear wave detection because shear wave propagation is relatively uniform along the depth direction. To obtain motion deep in the tissue, ultrasound with lower frequency can be used to achieve better penetration.
  • the long tone burst can be replaced with multiple short tone bursts that are interlaced with motion detection pulses.
  • the short tone bursts effectively represent a long push tone burst to tissues because the tissue response is relatively slow; therefore, the tissue does not recover from the each short tone burst before the next short tone bursts is applied. Detection pulses can, therefore, be added between these short tone bursts to measure tissue motion during the long push duration. Examples of methods of this nature are described, for example, in co-pending U.S. Provisional Patent Application No. 61/327,539, which is herein incorporated by reference in its entirety.
  • the short tone bursts used in the present method utilize unfocused ultrasound.
  • Limited diffraction beams can also be used to generate unfocused beams that extend over a large axial depth range.
  • Limited diffraction beams use all transducer elements to produce the unfocused beam and, therefore, can generate more tissue motion as a result of the more ultrasound energy present in the unfocused beam.
  • Previous methods for using limited diffraction beams require the use of an annular transducer array, or a two- dimensional transducer. With the present method, however, a one-dimensional, 1.5- dimensional, 1.75-dimensional, or two-dimensional transducer can be used to produce the unfocused push.
  • an ultrasonic imaging system 1300 includes a transducer array 1302 that includes a plurality of separately driven transducer elements 1304. When energized by a transmitter 1306, each transducer element 1302 produces a burst of ultrasonic energy. The ultrasonic energy reflected back to the transducer array 1302 from the object or subject under study is converted to an electrical signal by each transducer element 1304 and applied separately to a receiver 1308 through a set of switches 1310. The tran smitter 1306, receiver 1308, and switches 1310 are operated under the control of a digital controller 1312 responsive to the commands input by a human operator.
  • a complete scan is performed by acquiring a series of echo signals in which the switches 1310 are set to their transmit position, thereby directing the transmitter 1306 to be turned on momentarily to energize each transducer element 1304.
  • the switches 1310 are then set to their receive position and the subsequent echo signals produced by each transducer element 1304 are measured and applied to the receiver 1308.
  • the separate echo signals from each transducer element 1304 are combined in the receiver 1308 to produce a single echo signal that is employed to produce a line in an image, for example, on a display system 1314.
  • the transmitter 1306 drives the transducer array 1302 such that an ultrasonic beam is produced, and which is directed substantially perpendicular to the front surface of the transducer array 1302.
  • the present invention has been described with respect to the detection of shear waves with unfocused ultrasound, it will be appreciated by those skilled in the art that the present invention may also be applicable for detecting other tissue deformations resulting from an unfocused ultrasound push beam.
  • other imaging modalities may be used for detection.
  • the tissue deformation may be detected using optical detection, magnetic resonance imaging, microwave detection, and other electromagnetic detection techniques.

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Abstract

L'invention concerne des procédés de mesure des propriétés mécaniques d'un objet ou d'un sujet à examiner à l'aide d'un système ultrasonique et en utilisant une énergie ultrasonique non focalisée. Des ondes de cisaillement se propageant dans l'objet ou le sujet sont générées en appliquant une énergie ultrasonique non focalisée à l'objet ou au sujet, et des données de mesure sont acquises en appliquant une énergie ultrasonique focalisée ou non focalisée en au moins un endroit dans l'objet ou le sujet auquel les ondes de cisaillement sont présentes. Les propriétés mécaniques sont ensuite calculées à partir des données de mesure acquises.
PCT/US2012/026769 2011-02-25 2012-02-27 Vibrométrie ultrasonique avec ultrasons non focalisés WO2012116364A1 (fr)

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KR1020137025285A KR101929198B1 (ko) 2011-02-25 2012-02-27 비집속식 초음파에 의한 초음파 바이브로메트리
CN201280020131.5A CN103492855B (zh) 2011-02-25 2012-02-27 使用非聚焦超声的超声测振
JP2013555633A JP6067590B2 (ja) 2011-02-25 2012-02-27 非合焦超音波による超音波振動法
US14/001,604 US11172910B2 (en) 2011-02-25 2012-02-27 Ultrasound vibrometry with unfocused ultrasound
EP12749825.1A EP2678658B1 (fr) 2011-02-25 2012-02-27 Vibrométrie ultrasonique avec ultrasons non focalisés
BR112013021791-0A BR112013021791B1 (pt) 2011-02-25 2012-02-27 método para medir uma propriedade mecânica de um paciente com um sistema de ultrassom

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US11172910B2 (en) 2021-11-16
KR101929198B1 (ko) 2018-12-14
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BR112013021791A2 (pt) 2016-10-18
EP2678658A1 (fr) 2014-01-01
EP2678658A4 (fr) 2018-01-10
CN103492855B (zh) 2016-03-30
BR112013021791B1 (pt) 2020-11-17
KR20140034161A (ko) 2014-03-19
EP2678658B1 (fr) 2022-09-14
CN103492855A (zh) 2014-01-01
JP2014506523A (ja) 2014-03-17

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